Vessel sealing cutting assemblies

ABSTRACT

An endoscopic bipolar forceps includes a housing having a shaft affixed thereto the shaft including jaw members at a distal end thereof. The shaft includes a longitudinal axis defined therethrough and the jaw members are adapted to connect to a source of electrosurgical energy such that the jaw members are capable of conducting energy through tissue held therebetween to effect a tissue seal. A movable handle is included that is rotatable about a pivot to force a drive assembly to move the jaw members between the first and second positions. The pivot is located a fixed distance above the longitudinal axis. A cutting assembly is included having at least one blade element disposed within one of the jaw members. The blade element is selectively moveable from a first recessed position within the jaw member to a second extended position for cutting tissue. The cutting assembly also includes a remote actuator which reciprocates a camming element to move the blade element between the first and second positions.

CROSS REFERENCE TO RELATED APPLICATION

This application is a continuation-in-part of U.S. application Ser. Ser. No. 11/595,194, now U.S. Pat. No. 7,766,910, entitled “VESSEL SEALER AND DIVIDER FOR LARGE TISSUE STRUCTURES” filed Nov. 9, 2006 which claims the benefit of priority to U.S. Provisional Application Ser. No. 60/761,442 entitled “ENDOSCOPIC VESSEL SEALER AND DIVIDER FOR LARGE TISSUE STRUCTURES” filed Jan. 24, 2006. This application also claims the benefit of U.S. Provisional Application Ser. No. 60/994,449 entitled “VESSEL SEALING CUTTING ASSEMBLIES” filed Sep. 19, 2007 by Hixson et al. The entire contents of all of the above being incorporated by reference herein.

BACKGROUND

The present disclosure relates to an electrosurgical forceps and more particularly, the present disclosure relates to an endoscopic bipolar electrosurgical forceps for sealing and/or cutting large tissue structures.

TECHNICAL FIELD

Electrosurgical forceps utilize both mechanical clamping action and electrical energy to affect hemostasis by heating the tissue and blood vessels to coagulate, cauterize and/or seal tissue. Many surgical procedures require cutting and/or ligating large blood vessels and large tissue structures. Due to the inherent spatial considerations of the surgical cavity, surgeons often have difficulty suturing vessels or performing other traditional methods of controlling bleeding, e.g., clamping and/or tying-off transected blood vessels or tissue. By utilizing an elongated electrosurgical forceps, a surgeon can either cauterize, coagulate/desiccate and/or simply reduce or slow bleeding simply by controlling the intensity, frequency and duration of the electrosurgical energy applied through the jaw members to the tissue. Most small blood vessels, i.e., in the range below two millimeters in diameter, can often be closed using standard electrosurgical instruments and techniques. However, larger vessels can be more difficult to close using these standard techniques.

In order to resolve many of the known issues described above and other issues relevant to cauterization and coagulation, a recently developed technology has been developed by Valleylab, Inc. of Boulder, Colo., a division of Tyco Healthcare LP called vessel or tissue sealing. The process of coagulating vessels is fundamentally different than electrosurgical vessel sealing. For the purposes herein, “coagulation” is defined as a process of desiccating tissue wherein the tissue cells are ruptured and dried. “Vessel sealing” or “tissue sealing” is defined as the process of liquefying the collagen in the tissue so that it reforms into a fused mass with limited demarcation between opposing tissue structures. Coagulation of small vessels is sufficient to permanently close them, while larger vessels and tissue need to be sealed to assure permanent closure.

In order to effectively seal larger vessels (or tissue) two predominant mechanical parameters are accurately controlled—the pressure applied to the vessel (tissue) and the gap distance between the electrodes—both of which are affected by the thickness of the sealed vessel. More particularly, accurate application of pressure is important to oppose the walls of the vessel; to reduce the tissue impedance to a low enough value that allows enough electrosurgical energy through the tissue; to overcome the forces of expansion during tissue heating; and to contribute to the end tissue thickness which is an indication of a good seal.

As mentioned above, in order to properly and effectively seal larger vessels or tissue, a greater closure force between opposing jaw members is required. It is known that a large closure force between the jaws typically requires a large moment about the pivot for each jaw. This presents a design challenge because the jaw members are typically affixed with pins which are positioned to have small moment arms with respect to the pivot of each jaw member. A large force, coupled with a small moment arm, is undesirable because the large forces may shear the pins. As a result, designers compensate for these large closure forces by either designing instruments with metal pins and/or by designing instruments which at least partially offload these closure forces to reduce the chances of mechanical failure. As can be appreciated, if metal pivot pins are employed, the metal pins should be insulated to avoid the pin acting as an alternate current path between the jaw members which may prove detrimental to effective sealing.

Increasing the closure forces between electrodes may have other undesirable effects, e.g., it may cause the opposing electrodes to come into close contact with one another which may result in a short circuit and a small closure force may cause pre-mature movement of the tissue during compression and prior to activation.

As a result thereof, providing an instrument which consistently provides the appropriate closure force between opposing electrode within a preferred pressure range will enhance the chances of a successful seal. As can be appreciated, relying on a surgeon to manually provide the appropriate closure force within the appropriate range on a consistent basis would be difficult and the resultant effectiveness and quality of the seal may vary. Moreover, the overall success of creating an effective tissue seal is greatly reliant upon the user's expertise, vision, dexterity, and experience in judging the appropriate closure force to uniformly, consistently and effectively seal the vessel. In other words, the success of the seal would greatly depend upon the ultimate skill of the surgeon rather than the efficiency of the instrument.

It has been found that the pressure range for assuring a consistent and effective seal for large vessels and tissue structures is between about 3 kg/cm² to about 16 kg/cm² and, desirably, within a working range of 7 kg/cm² to 13 kg/cm². As can be appreciated, manufacturing an instrument which is capable of consistently providing a closure pressure within these working ranges is quite a design challenge for instrument manufacturers.

Various force-actuating assemblies have been developed in the past for providing the appropriate closure forces to affect vessel sealing. For example, one such actuating assembly has been developed by Valleylab, Inc. of Boulder, Colo., a division of Tyco Healthcare LP, for use with Valleylab's vessel sealing and dividing instrument for sealing large vessels and tissue structures commonly sold under the trademark Ligasure Atlas®. The Ligasure Atlas® is presently designed to fit through a 10 mm cannula and includes a bi-lateral jaw closure mechanism and is activated by a foot switch. Co-pending U.S. application Ser. Nos. 10/179,863 and 10/116,944 and PCT Application Serial Nos. PCT/US01/01890 and PCT/7201/11340 describe in detail the operating features of the Ligasure Atlas® and various methods relating thereto. The contents of all of these applications are hereby incorporated by reference herein.

Other force-actuating assemblies have also been developed by the Valleylab, Inc. of Boulder, Colo., a division of Tyco Healthcare LP, for use with Valleylab's vessel sealing and dividing instrument for sealing large vessels and tissue structures commonly sold under the trademark Ligasure 5 mm™. The Ligasure 5 mm™ is presently designed to fit through a 5 mm cannula and includes a unilateral jaw closure mechanism and is activated by a hand switch. Co-pending U.S. application Ser. Nos. 10/460,926 and 10/953,757 describe in detail the operating features of the Ligasure 5 mm™ and various methods relating thereto. The contents of both of these applications are hereby incorporated by reference herein.

It would be desirous to develop a vessel sealing instrument which consistently produces the required mechanical forces necessary to close the jaw members about very large tissue structures within a preferred pressure range. It would also be desirous for the instrument to provide a mechanical advantage for manipulating the jaw members and clamping tissue, such that, for example, the jaw members can be closed on tissue, easier, quicker and with less user force than previously envisioned to clamp the tissue.

SUMMARY

The forceps includes a housing, a shaft having a longitudinal axis defined therethrough, a drive assembly and a movable handle. The shaft includes an end effector assembly having a pair of jaw members attached to a distal end thereof. The jaw members are movable from a first position in spaced relation to one another to at least a second position closer to one another. The jaw members are for grasping tissue therebetween. Each of the jaw members is adapted to connect to an electrosurgical energy source, thus enabling the jaw members to conduct energy through tissue held between the jaw members to create a tissue seal.

The drive assembly moves the jaw members relative to one another from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members are closer to one another for manipulating tissue. The movable handle is rotatable about a pivot to force a drive flange of the drive assembly to move the jaw members between the first and second positions. The pivot is located a fixed distance above the longitudinal axis and the drive flange is located generally along the longitudinal axis. This mechanical arrangement creates level-like mechanical advantage about the pivot to facilitate closing the jaw members about tissue. The forceps also includes a knife assembly having a generally t-shaped movable knife bar that is dimensioned to operatively engage a corresponding slot defined within the housing. The slot guides the movement of the knife bar during translation thereof.

In one embodiment, the knife bar is operatively coupled to a knife slidingly disposed within the shaft. The forceps further includes a finger actuator operatively coupled to the knife assembly wherein movement of the finger actuator moves the knife bar which, in turn, moves the knife to cut tissue disposed between the jaw members. In another embodiment, the shaft includes a drive sleeve slidingly disposed therein that operatively connects to the drive assembly for moving the jaw members and the knife assembly includes a cuff at the distal end of the knife bar. The cuff is dimensioned to encapsulate and move atop the drive sleeve upon movement of the knife bar. The forceps may also include a finger actuator operatively connected to the knife assembly. The finger actuator includes two generally u-shaped flanges that rotate about a pivot to abut and force the cuff distally which, in turn, results in distal translation of the knife bar.

In yet another embodiment, a spring is included which biases the knife assembly in a proximal-most orientation. A rotating assembly is also included and is configured to rotate the jaw members about the longitudinal axis defined through the shaft. A hand switch may also be included within the housing which is adapted to connect to the source of electrosurgical energy. The hand switch allows a user to selectively supply bipolar energy to the jaw members to affect a tissue seal. At least one of the jaw members includes a series of stop members disposed thereon for regulating the distance between the jaw members during sealing.

The present disclosure also relates to a bipolar forceps that includes a housing having a shaft affixed thereto. The shaft includes jaw members attached at a distal end thereof having a longitudinal axis defined therethrough. The jaw members are adapted to connect to a source of electrosurgical energy such that the jaw members are capable of conducting energy through tissue held therebetween to effect a tissue seal. The forceps also includes a drive assembly that moves the jaw member relative to one another about a pivot from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members are closer to one another for manipulating tissue.

A movable handle is included which is rotatable about a pivot to force a drive flange of the drive assembly to move the jaw members between the first and second positions. The pivot is located a fixed distance above the longitudinal axis and the drive flange is located generally along the longitudinal axis. A trigger assembly is included that is operatively coupled to the housing and operatively coupled to a knife assembly. The knife assembly includes a drive rod which, upon actuation of the trigger assembly, selectively translates a knife through tissue disposed between the jaw members. A knife guide may also be included that is dimensioned to facilitate alignment and translation of the knife through and into a knife channel defined between the jaw members.

In one embodiment, the knife guide includes two engageable halves that insulate the jaw members from one another. The knife guide may also include one or more apertures defined therein that allow the pivot to extend therethrough. The drive assembly may also include a cam pin at a distal end thereof that operatively engages the jaw members and the knife guide may be configured to include one or more slots defined therein that allow the cam pin to extend therethrough.

In another embodiment, the pivot includes an aperture defined therein that allows the knife to extend therethrough. The pivot may include a stem and a cap that matingly engage on opposite sides of the shaft to secure the jaw members during assembly.

In still yet another embodiment, the trigger assembly selectively translates the knife through tissue disposed between the jaw members and the knife assembly includes a knife carriage having a t-shaped distal end that engages the trigger assembly and a proximal end that engages a knife bar slidingly mounted within the housing. The knife bar may include a cuff at a distal end thereof that defines an aperture located therethrough. The shaft is dimensioned to rotate and slide through the aperture of the cuff.

The drive assembly may further include a cam pin that operatively couples the distal end of the drive sleeve to the jaw members for actuation thereof. The knife may be dimensioned to include a slot defined therein that allows the cam pin to extend therethrough.

Another embodiment includes an endoscopic bipolar forceps having a housing with a shaft affixed thereto, the shaft including jaw members at a distal end thereof. The shaft includes a longitudinal axis defined therethrough and the jaw members are adapted to connect to a source of electrosurgical energy such that the jaw members are capable of conducting energy through tissue held therebetween to effect a tissue seal. The forceps also includes a drive assembly which moves the jaw member relative to one another from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members are closer to one another for manipulating tissue. A movable handle is included that is rotatable about a pivot to force the drive assembly to move the jaw members between the first and second positions. The pivot is located a fixed distance above the longitudinal axis. A cutting assembly is included having at least one blade element disposed within one of the jaw members. The blade element is selectively moveable from a first recessed position within the jaw member to a second extended position for cutting tissue. The cutting assembly also includes a remote actuator that reciprocates a camming element to move the blade element between the first and second positions.

The blade element may be dimensioned to include a plurality of perforating sections that are configured to perforate tissue upon actuation of the actuator. The actuator may include a sleeve that is selectively movable over the jaw members to cam the blade element into tissue. A spring may also be utilized to bias the blade element in a recessed configuration.

In another embodiment, the cutting assembly includes a pizza-like cutting wheel for dividing tissue. In yet another envisioned embodiment, a hand switch may be disposed within the housing and adapted to connect to the source of electrosurgical energy. The hand switch is configured to allow a user to selectively supply bipolar energy to the jaw members to effect a tissue seal. At least one of the jaw members may include a series of stop members disposed thereon for regulating the distance between the jaw members during sealing.

In yet still another embodiment, the cutting assembly may include at least one blade element which extends from a side of at least one of the jaw members such that rotation of the jaw member about the longitudinal axis against tissue will cause the blade element to divide tissue. The cutting assembly may also include a pliable, wedge-like blade element disposed at a proximal end of the jaw members. The wedge-like blade element is configured to be expandable from a first closed configuration when the jaw members are closed about tissue to an expanded cutting configuration when the jaw members are opened and forced distally through tissue.

BRIEF DESCRIPTION OF THE DRAWINGS

Various embodiments of the subject instrument are described herein with reference to the drawings wherein:

FIG. 1A is a perspective view of a bipolar forceps shown in open configuration and including a housing, a shaft, handle assembly, trigger assembly and an end effector assembly according to the present disclosure;

FIG. 1B is a perspective view of the bipolar forceps of FIG. 1A shown in closed configuration;

FIG. 2 is a rear view of the forceps of FIG. 1A;

FIG. 3A is an enlarged, front perspective view of the end effector assembly of FIG. 1A shown in an open configuration;

FIG. 3B is an enlarged, front perspective view of the end effector assembly of FIG. 1A shown in a closed configuration;

FIG. 3C is an enlarged, side view of the end effector assembly of FIG. 1A shown in open configuration;

FIG. 3D is an enlarge, front view of the end effector assembly of FIG. 1A shown in open configuration;

FIG. 3E is a greatly-enlarged, exploded perspective view of the top jaw member;

FIG. 3F is a greatly-enlarged, exploded perspective view of the bottom jaw member;

FIG. 4 is a perspective view of the endoscopic forceps of FIG. 1A with the internal working components of the forceps exposed;

FIG. 5A is side view of the endoscopic forceps of FIG. 1A with the internal working components of the forceps exposed;

FIG. 5B is side view of the endoscopic forceps of FIG. 1B with the internal working components of the forceps exposed;

FIG. 5C is a greatly-enlarged, perspective view of the handle assembly in open configuration;

FIG. 5D is a greatly-enlarged, perspective view of the handle assembly in closed configuration;

FIG. 6A is an internal, perspective view of the endoscopic forceps of FIG. 1B with the internal working components of the forceps exposed and the trigger shown in an un-actuated position;

FIG. 6B is an internal, perspective view of the endoscopic forceps of FIG. 1B with the internal working components of the forceps exposed and the trigger shown in an actuated position;

FIG. 6C is a schematic representation of the electrical configuration for the trigger assembly;

FIG. 7 is an internal, side view of the endoscopic forceps of FIG. 1B with the trigger shown in an actuated position;

FIG. 8A is a side cross-sectional view showing the trigger in an actuated position;

FIG. 8B is an enlarged, side cross-sectional view showing the jaw members in a spaced apart orientation;

FIG. 8C is an enlarged, side cross-sectional view showing the jaw members in a closed orientation;

FIG. 9A is side cross-sectional view of the housing showing both the trigger and the handle un-actuated;

FIG. 9B is side cross-sectional view of the housing showing both the trigger and the handle actuated;

FIG. 10A is an enlarged, side cross-sectional view showing the end effector in a closed position and the knife in an unactuated position;

FIG. 10B is an enlarged, side cross-sectional view showing the end effector in a closed position and the knife in an actuated position;

FIG. 10C is an enlarged, front perspective view of a bottom jaw member of the end effector assembly showing the knife in an unactuated position;

FIG. 10D is an enlarged, front perspective view of the bottom jaw member showing the knife in an actuated position;

FIG. 11 is an exploded, perspective view of the forceps of FIG. 1A;

FIG. 12 is an enlarged, exploded perspective view of the housing;

FIG. 13 is an enlarged, exploded perspective view of the end effector assembly and the shaft;

FIG. 14 is a greatly enlarged, exploded perspective view of the end effector assembly; and

FIGS. 15A-15M show schematic side views of various cutting assemblies for use with the forces of the present disclosure.

DETAILED DESCRIPTION

Turning now to FIGS. 1A-2, one embodiment of a bipolar forceps 10 is shown for use with various surgical procedures and generally includes a housing 20, a handle assembly 30, a rotating assembly 80, a trigger assembly 70 and an end effector assembly 100 which mutually cooperate to grasp, seal and divide large tubular vessels and large vascular tissues. Although the majority of the figure drawings depict a bipolar forceps 10 for use in connection with endoscopic surgical procedures, the present disclosure may be used for more traditional open surgical procedures. For the purposes herein, the forceps 10 is described in terms of an endoscopic instrument, however, it is contemplated that an open version of the forceps may also include the same or similar operating components and features as described below.

Forceps 10 includes a shaft 12 which has a distal end 16 dimensioned to mechanically engage the end effector assembly 100 and a proximal end 14 which mechanically engages the housing 20. Details of how the shaft 12 connects to the end effector are described in more detail below with respect to FIGS. 13 and 14. The proximal end 14 of shaft 12 is received within the housing 20 and the connections relating thereto are also described in detail below with respect to FIGS. 11 and 12. In the drawings and in the descriptions which follow, the term “proximal,” as is traditional, will refer to the end of the forceps 10 which is closer to the user, while the term “distal” will refer to the end which is farther from the user.

As best seen in FIGS. 1A and 2, forceps 10 also includes an electrosurgical cable 310 which connects the forceps 10 to a source of electrosurgical energy, e.g., a generator 500 (shown schematically). It is contemplated that generators such as those sold by Valleylab—a division of Tyco Healthcare LP, located in Boulder Colo. may be used as a source of electrosurgical energy, e.g., Ligasure™ Generator, FORCE EZ™ Electrosurgical Generator, FORCE FX™ Electrosurgical Generator, FORCE 1C™, FORCE 2™ Generator, SurgiStat™ II or other envisioned generators which may perform different or enhanced functions. One such system is described in commonly-owned U.S. Pat. No. 6,033,399 entitled “ELECTROSURGICAL GENERATOR WITH ADAPTIVE POWER CONTROL” the entire contents of which are hereby incorporated by reference herein. Other systems have been described in commonly-owned U.S. Pat. No. 6,187,003 entitled “BIPOLAR ELECTROSURGICAL INSTRUMENT FOR SEALING VESSELS” the entire contents of which are also incorporated by reference herein.

In one embodiment, the generator 500 includes various safety and performance features including isolated output, independent activation of accessories. It is envisioned that the electrosurgical generator includes Valleylab's Instant Response™ technology features which provides an advanced feedback system to sense changes in tissue 200 times per second and adjust voltage and current to maintain appropriate power. The Instant Response™ technology is believed to provide one or more of the following benefits to surgical procedure:

-   -   Consistent clinical effect through all tissue types;     -   Reduced thermal spread and risk of collateral tissue damage;     -   Less need to “turn up the generator”; and     -   Designed for the minimally invasive environment.

Cable 310 is internally divided into cable leads 310 a, 310 b and 325 b which are designed to transmit electrical potentials through their respective feed paths through the forceps 10 to the end effector assembly 100. More particularly, cable feed 325 b connects through the forceps housing 20 and through the rotating assembly to jaw member 120. Lead 310 a connects to one side of the switch 60 and lead 310 c connects to the opposite side of the switch 60 such that upon activation of the switch energy is transmitted from lead 310 a to 310 c. Lead 310 c is spliced with lead 310 b which connects through the rotating assembly to jaw member 110 (See FIG. 6C). Details relating to the electrical connections are explained in more detail below with the discussion of the switch 60.

Handle assembly 30 includes a fixed handle 50 and a movable handle 40. Fixed handle 50 is integrally associated with housing 20 and handle 40 is movable relative to fixed handle 50 as explained in more detail below with respect to the operation of the forceps 10. Fixed handle 50 is oriented approximately 30 degrees relative a longitudinal axis “A-A” defined through shaft 12. Fixed handle 50 may include one or more ergonomic enhancing elements to facilitate handling, e.g., scallops, protuberances, elastomeric material, etc.

Rotating assembly 80 is operatively associated with the housing 20 and is rotatable approximately 180 degrees about a longitudinal axis “A-A” (See FIG. 1A). Details of the rotating assembly 80 are described in more detail with respect to FIG. 11.

As mentioned above, end effector assembly 100 is attached at the distal end 14 of shaft 12 and includes a pair of opposing jaw members 110 and 120. Movable handle 40 of handle assembly 30 is ultimately connected to a drive assembly 130 which, together, mechanically cooperate to impart movement of the jaw members 110 and 120 from an open position wherein the jaw members 110 and 120 are disposed in spaced relation relative to one another, to a clamping or closed position wherein the jaw members 110 and 120 cooperate to grasp tissue therebetween.

It is envisioned that the forceps 10 may be designed such that it is fully or partially disposable depending upon a particular purpose or to achieve a particular result. For example, end effector assembly 100 may be selectively and releasably engageable with the distal end 16 of the shaft 12 and/or the proximal end 14 of shaft 12 may be selectively and releasably engageable with the housing 20 and the handle assembly 30. In either of these two instances, the forceps 10 would be considered “partially disposable” or “reposable”, i.e., a new or different end effector assembly 100 (or end effector assembly 100 and shaft 12) selectively replaces the old end effector assembly 100 as needed. As can be appreciated, the presently disclosed electrical connections would have to be altered to modify the instrument to a reposable forceps.

Turning now to the more detailed features of the present disclosure as described with respect to FIGS. 1A-14, movable handle 40 includes a finger loop 43 which has an aperture 41 defined therethrough which enables a user to grasp and move the handle 40 relative to the fixed handle 50. Finger loop 43 is typically ergonomically enhanced and may include one or more gripping elements (not shown) disposed along the inner peripheral edge of aperture 41 which are designed to facilitate gripping of the movable handle 40 during activation, e.g., a so called “soft touch” material. Gripping elements may include one or more protuberances, scallops and/or ribs to enhance gripping.

As best seen in FIGS. 5A and 5B, movable handle 40 is selectively movable about a pivot pin 45 a from a first position relative to fixed handle 50 to a second position in closer proximity to the fixed handle 50 which, as explained below, imparts movement of the jaw members 110 and 120 relative to one another. The movable handle includes a clevis 46 which forms a pair of upper flanges 46 a and 46 b each having an aperture at an upper end thereof for receiving a pivot pin 45 (See FIG. 12) therethrough and mounting the upper end of the handle 40 to the housing 20. In turn, pivot pin 45 mounts to respective housing halves 20 a and 20 b. Pivot pin 45 is dimensioned to mount within socket 45 a of housing half 20 b.

Each upper flange 46 a and 46 b also includes a force-actuating flange or drive flange 47 a and 47 b (See FIG. 7), respectively, which are aligned along longitudinal axis “A” and which abut the drive assembly 130 such that pivotal movement of the handle 40 forces actuating flanges 47 a and 47 b against the drive assembly 130 which, in turn, closes the jaw members 110 and 120 (See FIGS. 5A and 5B). For the purposes herein, 47 a and 47 b which act simultaneously on the drive assembly 130 are referred to as “driving flange 47”. A more detailed explanation of the inter-cooperating components of the handle assembly 30 and the drive assembly 130 is discussed below.

As best shown in FIG. 5C, the lower end of the movable handle 40 includes a flange 42 which is typically integrally associated with or operatively connected to movable handle 40. Flange 42 is typically T-shaped and includes a pin-like element 44 which projects laterally or transversally from a distal end thereof and is configured to engage a corresponding railway 55 disposed within fixed handle 50. More particularly, the pin 44 is configured to ride within a pre-defined channel 53 disposed within the railway 55 to lock the movable handle 40 relative to the fixed handle 50 upon reciprocation thereof. Additional features with respect to the t-shaped pin 44 are explained below in the detailed discussion of the operational features of the forceps 10.

Movable handle 40 is designed to provide a distinct mechanical advantage over conventional handle assemblies due to the unique position of the pivot pin 45 (i.e., pivot point) relative to the longitudinal axis “A” of the shaft 12 and the disposition of the driving flange 47 along longitudinal axis “A”. In other words, it is envisioned that by positioning the pivot pin 45 above the driving flange 47, the user gains lever-like mechanical advantage to actuate the jaw members 110 and 120 enabling the user to close the jaw members 110 and 120 with lesser force while still generating the required forces necessary to effect a proper and effective tissue seal.

As shown best in FIGS. 3A-3F, 13 and 14, the end effector assembly 100 includes opposing jaw members 110 and 120 which cooperate to effectively grasp tissue for sealing purposes. The end effector assembly 100 is designed as a bilateral assembly, i.e., both jaw members 110 and 120 pivot relative to one another about a pivot pin 95 disposed therethrough. The jaw members 110 and 120 are curved to facilitate manipulation of tissue and to provide better “line of sight” for accessing organs and large tissue structures.

A reciprocating drive sleeve 134 is slidingly disposed within the shaft 12 and is remotely operable by the drive assembly 130 as explained in more detail below. Drive sleeve 134 includes a bifurcated distal end composed of halves 134 a and 134 b, respectively, which define a cavity 134′ therebetween for receiving jaw members 110 and 120. More particularly and as best illustrated in FIGS. 13 and 14, jaw members 110 and 120 include proximal flanges 113 and 123, respectively, which each include an elongated angled slot 117 and 127, respectively, defined therethrough. A drive pin 139 (See FIG. 13) mounts jaw members 110 and 120 to the end of a sleeve 134 and within cavity 134′ disposed between flanges 134 a and 134 b. Cam pin or drive pin 139 mounts through apertures 139 a and 139 b defined in flanges 134 a and 134 b, respectively, and is reciprocable within slots 16 a′ and 16 b′ disposed at the distal ends 16 a and 16 b of shaft 12 (See FIG. 14). It is envisioned that slots 16 a′ and 16 b′ may extend into aperture 95′ and 95″ to facilitate assembly of pin 139. Pin 139 may be composed of two mechanically interfacing elements which are dimensioned to frictionally receive one another to retain pin 139 in place once assembled.

Alternatively or in addition, pin 139 may be held in place by one of several known manufacturing techniques including: laser or heat-based welding, press-fit mechanical interaction (or other mechanically interlocking geometry, adhesives, chemical bonding, etc. A component disposed on the outside of shaft 12 may also be utilized to retain the pin 139 in place once assembled. For example, a heat shrink material, adhesive tape, rubber or other insulating boot or silicone may be used for this purpose. It is also envisioned that a varying diameter version of pin 139 may be utilized to prevent the pin from coming loose once assembled. It is also envisioned that a cap or stem (not shown) arrangement may be employed for this purpose as well.

Drive sleeve 134, which ultimately connects to the drive assembly 130, is dimensioned to slidingly receive knife drive rod 193, knife 190 and posts 171 a and 171 b of halves 170 a and 170 b of knife guide 170. Drive sleeve 134, in turn, is received within shaft 12. Upon actuation of the drive assembly 130, the drive sleeve 134 reciprocates which, in turn, causes the drive pin 139 to ride within slots 117 and 127 to open and close the jaw members 110 and 120 as desired. The jaw members 110 and 120, in turn, pivot about pivot pin 95 disposed through respective pivot holes 113 a and 123 a disposed within flanges 113 and 123. As can be appreciated, squeezing handle 40 toward handle 50 pulls drive sleeve 134 and drive pin 139 proximally to close the jaw members 110 and 120 about tissue grasped therebetween and pushing the sleeve 134 distally opens the jaw members 110 and 120 for grasping purposes.

Turning back to the details of the jaw member 110 and 120 as best shown in FIGS. 3A-3F, jaw member 110 includes a support base 119 which extends distally from flange 113 and which is dimensioned to support an insulative plate 119′ thereon. Insulative plate 119′, in turn, is configured to support an electrically conductive tissue engaging surface or sealing plate 112 thereon. It is contemplated that the sealing plate 112 may be affixed atop the insulative plate 119′ and support base 119 in any known manner in the art, snap-fit, over-molding, stamping, ultrasonically welded, etc. Support base 119 together with the insulative plate 119′ and electrically conductive tissue engaging surface 112 are encapsulated by an outer insulative housing 116. Outer housing 116 includes a cavity 116 a which is dimensioned to securely engage the electrically conductive sealing surface 112 as well as the support base 119 and insulative plate 119′. This may be accomplished by stamping, by overmolding, by overmolding a stamped electrically conductive sealing plate and/or by overmolding a metal injection molded seal plate or other more common methods known in the art (i.e., a conductive surface bound to a structural support via an insulating material). All of these manufacturing techniques produce jaw member 110 having an electrically conductive surface 112 which is substantially surrounded by an insulating housing or substrate 116.

For example and as shown in FIG. 3E, the electrically conductive sealing plate 112 includes a peripheral flange 112 a which surrounds the periphery of the sealing plate 112. Flange 112 a is designed to matingly engage an inner lip 116 b of the outer insulator 116. Again, this may be accomplished by any of the aforementioned known processes, e.g., overmolding. It is envisioned that lead 310 b which extends from switch 60 (See FIG. 6C) terminates within the outer insulator 116 and is designed to electro-mechanically couple to the sealing plate 112 by virtue of a crimp-like connection 326 a. Insulator 119′, electrically conductive sealing surface 112 and the outer, non-conductive jaw housing 116 are preferably dimensioned to limit and/or reduce many of the known undesirable effects related to tissue sealing, e.g., flashover, thermal spread and stray current dissipation.

It is envisioned that the electrically conductive sealing surface 112 may also include an outer peripheral edge which has a pre-defined radius and the outer housing 116 meets the electrically conductive sealing surface 112 along an adjoining edge of the sealing surface 112 in a generally tangential position. At the interface, the electrically conductive surface 112 is raised relative to the outer housing 116. These and other envisioned embodiments are discussed in co-pending, commonly assigned Application Serial No. PCT/US01/11412 entitled “ELECTROSURGICAL INSTRUMENT WHICH REDUCES COLLATERAL DAMAGE TO ADJACENT TISSUE” by Johnson et al. and co-pending, commonly assigned Application Serial No. PCT/US01/11411 entitled “ELECTROSURGICAL INSTRUMENT WHICH IS DESIGNED TO REDUCE THE INCIDENCE OF FLASHOVER” by Johnson et al., the entire contents of both of which being hereby incorporated by reference herein.

The electrically conductive surface or sealing plate 112 and the outer housing 116, when assembled, form a longitudinally-oriented slot 115 a defined therethrough for reciprocation of the knife blade 190 (See FIG. 13). It is envisioned that knife slot 115 a cooperates with a corresponding knife slot 115 b defined in jaw member 120 to facilitate longitudinal extension of the knife blade 190 along a preferred cutting plane to effectively and accurately separate the tissue along the formed tissue seal. Together, knife slots 115 a and 115 b form knife channel 115 for reciprocation of the knife 190. As best illustrated in FIGS. 3A-3F, knife channel 115 runs through the center of the jaw members 110 and 120, respectively, such that a blade 190 from the knife assembly 70 can cut the tissue grasped between the jaw members 110 and 120 when the jaw members 110 and 120 are in a closed position. As described in more detail below, handle 30 a includes a passive lockout flange 49′ which prevents actuation of the knife assembly 70 when the handle 40 is open thus preventing accidental or premature activation of the blade 190 through the tissue. In addition, the passive lockout flange 49′ is dimensioned to force the trigger 70 to retract the knife 190 when the handle 40 is moved to an open position.

As explained above and as illustrated in FIGS. 3F, 8B, 8C, 10C and 10D, the knife channel 115 is formed when the jaw members 110 and 120 are closed. In other words, the knife channel 115 includes two knife channel halves—knife slot 115 a disposed in sealing plate 112 of jaw member 110 and knife slot 15 b disposed sealing plate 122 of jaw member 120. It is envisioned that the knife channel 115 may be dimensioned to include some degree of curvature to cause the knife 190 to move through tissue in a curved fashion. Alternatively, the knife channel 115 may be configured as a straight slot with no degree of curvature which, in turn, causes the knife 190 to move through the tissue in a substantially straight fashion. Insulating plate 119′ also forms part of the knife channel 115 and includes slot 115 a′ defined therein which extends along insulating plate 119′ and which aligns in vertical registration with knife slot 115 a to facilitate translation of distal end 192 of the knife 190 therethrough.

As mentioned above, end effector assembly 100 also includes knife guide 170 which is dimensioned to facilitate alignment and translation of the knife 190 through and into the knife channel 115. More particularly, knife guide 170 includes half 170 a and half 170 b which mechanically interface to encapsulate the knife 190 upon assembly (See FIG. 13). It is envisioned that knife guide 170, once assembled, aligns the knife 190 for facile translation through knife channel 115 upon reciprocation of a knife drive rod 193 (FIG. 13). The operation of the drive rod 193 is described below with reference to the operational features of the forceps 10. Each half 170 a and 170 b of the knife guide 170 includes various interfaces thereon and apertures defined therein which allow unencumbered movement of the various operating features of the end effector assembly 100, e.g., pivot 95, drive pin 139 and knife 190. More particularly, halves 170 a and 170 b include apertures 173 a and 173 b, respectively, defined therethrough which allow passage of the pivot 95 during assembly. Halves 170 a and 170 b also include laterally-aligned slots 172 a and 172 b defined therein which allow reciprocation of the drive pin 139 upon opening and closing of the jaw members 110 and 120. One or more guides 327 (FIG. 14) may also be included to guide leads, e.g., lead 325 a, along knife guide 170 and to the electrically conductive plates, e.g., plate 122. Knife guide halves 170 a and 170 b also include posts 171 a and 171 b which extend proximally into slot 16′ upon assembly to engage knife 190.

Knife channel 115 runs through the center of the jaw members 110 and 120, respectively, such that a distal end 192 of the knife 190 can cut the tissue grasped between the jaw members 110 and 120 when the jaw members 110 and 120 are in a closed position. More particularly and as described in more detail below with respect to the operation of the forceps 10, the knife 190 can only be advanced through the tissue when the jaw members 110 and 120 are closed thus preventing accidental or premature activation of the knife 190 through the tissue. Passive lockout flange 49′ detailed below prevents unintended translation of the knife 190 while the jaw members 110 and 120 are disposed in an open configuration. It is also envisioned that the knife 190 be dimensioned to allow other components to pass therethrough which additionally creates the benefit of enhancing the overall flexibility of the knife to facilitate passage through the knife channel 115.

Alternatively, one or both jaw members may also include a safety lockout to prevent the knife 190 from advancing while the jaw members are in an open configuration. Various safety lockout configurations are disclosed in commonly owned, co-pending U.S. application Ser. No. 10/962,116 entitled “OPEN VESSEL SEALING INSTRUMENT WITH CUTTING MECHANISM AND DISTAL LOCKOUT” and commonly owned, co-pending U.S. Provisional Application Ser. No. 60/722,177 entitled “IN-LINE VESSEL SEALER AND DIVIDER”, the entire contents of which are both incorporated by reference herein.

Jaw member 120 includes similar elements to jaw member 110 such as jaw housing 126 which encapsulates a support plate 129, an insulator plate 129′ and an electrically conductive sealing surface 122. Likewise, the electrically conductive surface 122 and the insulator plate 129′, when assembled, include respective longitudinally-oriented knife slots 115 b and 115 b′ defined therethrough for reciprocation of the knife blade 190. As mentioned above, when the jaw members 110 and 120 are closed about tissue, knife slots 115 a and 115 b form a complete knife channel 115 to allow longitudinal extension of the knife 190 in a distal fashion to sever tissue along a tissue seal. It is also envisioned that the knife channel 115 may be completely disposed in one of the two jaw members, e.g., jaw member 120, depending upon a particular purpose. It is also envisioned that jaw member 120 may be assembled in a similar manner as described above with respect to jaw member 110. More particularly, the sealing plate 122 may be dimensioned to include an outer peripheral rim 122 a which is dimensioned to mechanically interface with an inner lip 126 b of housing 126 to secure the sealing plate 122 to the housing 126 with plates 129 and 129′ encapsulated therein.

As best seen in FIG. 3F, jaw member 120 includes a series of stop members 90 disposed on the inner facing surface of the electrically conductive sealing surface 122 to facilitate gripping and manipulation of tissue and to define a gap “G” (FIG. 10B) between opposing jaw members 110 and 120 during sealing and cutting of tissue. It is envisioned that the series of stop members 90 may be employed on one or both jaw members 110 and 120 depending upon a particular purpose or to achieve a desired result. A detailed discussion of these and other envisioned stop members 90 as well as various manufacturing and assembling processes for attaching and/or affixing the stop members 90 to the electrically conductive sealing surfaces 112, 122 are described in commonly-assigned, co-pending U.S. Application Serial No. PCT/US01/11413 entitled “VESSEL SEALER AND DIVIDER WITH NON-CONDUCTIVE STOP MEMBERS” by Dycus et al. which is hereby incorporated by reference in its entirety herein.

Jaw member 120 is connected to a second electrical lead 325 b extending from switch 60 (See FIG. 6B) which terminates within the jaw housing 126 and is designed to electro-mechanically couple to the sealing plate 122 by virtue of a crimp-like connection 326 b. As explained in more detail below, leads 310 b and 325 b allow a user to selectively supply bipolar electrosurgical energy to the jaw members 110 and 120 as needed during surgery.

Jaw members 110 and 120 are electrically isolated from one another such that electrosurgical energy can be effectively transferred through the tissue to form a tissue seal. For example and as best illustrated in FIGS. 3A-3F, each jaw member 110 and 120 includes a uniquely-designed electrosurgical cable path which transmits electrosurgical energy through the cable leads 310 b and 325 b to the electrically conductive sealing surfaces 112 and 122, respectively. Cable leads 310 b and 325 b are held loosely but securely along the cable path to permit rotation of the jaw members 110 and 120. As can be appreciated, this isolates electrically conductive sealing surfaces 112 and 122 from the remaining operative components of the end effector assembly 100 and shaft 12. The two electrical potentials are isolated from one another by virtue of the insulative sheathing surrounding the cable leads 310 b and 325 b.

Jaw members 110 and 120 are engaged to the end of rotating shaft 12 by pivot pin 95 such that rotation of the rotating assembly 80 correspondingly rotates shaft 12 (along with sleeve 134 and knife 190) which, in turn, rotates end effector assembly 100 (See FIG. 1A). More particularly, the distal end of rotating shaft 12 is bifurcated to include ends 16 a and 11 b which define a channel 16′ therein for receiving jaw members 110 and 120. Pivot pin 95 includes a stem 95 a and cap 95 b arrangement which is dimensioned to engage through aperture 95′ and 95″ disposed in ends 16 b and 16 a, respectively. Upon assembly and as best illustrated in FIGS. 13 and 14, the stem 95 a of pivot pin 95 extends, in order, through end 16 a of shaft 12, aperture 123 a of jaw member 120, aperture 173 a of half 170 a or knife guide 170, aperture 173 b of half 170 b of knife guide 170, aperture 113 a of jaw member 110 and end 16 b of shaft 12 to engage cap 95 b. Slots 16 a′ and 16 b′ are defined within distal ends 16 a and 16 b and are dimensioned to allow reciprocation of drive pin 139 therein. Stem 95 a includes a pass through hole 96 defined therein which allows passage of the knife 190 therethrough for severing tissue while still allowing a large rotational surface area for the jaw members during loading.

Turning now to the cooperating components of the housing, FIGS. 5A, 5B, 6A, 6B, 11 and 12 show the details of the housing 20 and the component features thereof, namely, the drive assembly 130, the rotating assembly 80, the knife actuating assembly 160, the trigger assembly 70 and the handles 40 and 50. More particularly, FIGS. 5A and 5B show the above-identified assemblies and components in an assembled form in the housing 20 and FIGS. 11 and 12 show an exploded view of each of the above-identified assemblies and components.

As mentioned above and as best shown in FIGS. 11 and 12, the proximal end of shaft 12 is mechanically engaged to the housing 20. Housing 20 is formed from two (2) housing halves 20 a and 20 b which each include a plurality of interfaces which are dimensioned to mechanically align and engage one another to form housing 20 and enclose the internal working components of forceps 10. As can be appreciated, fixed handle 50 which, as mentioned above, is integrally associated with housing 20, includes halves 50 a and 60 b which take the shape of handle 50 upon the assembly of the housing halves 20 a and 20 b.

It is envisioned that a plurality of additional interfaces (not shown) may disposed at various points around the periphery of housing halves 20 a and 20 b for ultrasonic welding purposes, e.g., energy direction/deflection points. It is contemplated that ultrasonic welding provides better dimensional stability, strength and joint reliability that other, more traditional, methods. For example, the housing halves may be ultrasonically welded utilizing a combination of a primary weld joint using traditional triangular (or similar) energy directors to form a bonded joint coupled with a secondary hard stop surface (removed from the primary joint surface) for preventing over compression of the joint. A tertiary set of alignment pins may be utilized throughout the housing halves 20 a and 20 b which are configured to both accurately align the halves 20 a and 20 b during assembly and provide strength and stability during manufacture, handling and transport.

It is also contemplated that housing halves 20 a and 20 b (as well as the other components described below) may be assembled together in any fashion known in the art. For example, alignment pins, snap-like interfaces, tongue and groove interfaces, locking tabs, adhesive ports, etc. may all be utilized either alone or in combination for assembly purposes.

As best seen in FIGS. 11 and 12, rotating assembly 80 includes two C-shaped halves 80 a and 80 b which, when assembled, form the rotating assembly 80 which, in turn, house the drive assembly 130 and the knife actuating assembly 160. Half 80 a includes a series of detents/flanges (not shown) which are dimensioned to engage a pair of corresponding sockets or other mechanical interfaces (not shown) disposed within rotating half 80 b. Half 80 a also includes a tab 84 a (phantomly illustrated) which together with a corresponding tab 84 b disposed on half 80 b cooperate to matingly engage slot 80′ disposed on shaft 12. As can be appreciated, this permits selective rotation of the shaft 12 about axis “A-A” by manipulating the rotating member 80 in the direction of the arrow “B”, which, in turn, rotates the end effector assembly in the direction of arrow “C” (See FIG. 1A). The rotating assembly may include one or more mechanical interfaces which essentially lock the rotating assembly in a fully counter-clock wise rotational position or a fully clockwise rotational position. It is envisioned that this will allow left-handed or right-handed orientations for the end effector assembly for particular users.

As mentioned above and as best illustrated in FIGS. 5A, 5B, 6A and 6B, the movable handle 40 includes clevis 46 which forms upper flanges 46 a and 46 b which pivot about pins 45 a and 45 b to pull the reciprocating sleeve 134 along longitudinal axis “A-A” and force driving flanges 47 a and 47 b against the drive assembly 130 which, in turn, closes the jaw members 110 and 120. The various moving relationships of the flanges 47 a and 47 b and the drive assembly 130 are explained in more detail below with respect to the operation of the forceps 10. The arrangement of the driving flanges 47 a and 47 b and the pivot point 45 of the movable handle 40 provides a distinct mechanical advantage over conventional handle assemblies due to the unique position of the pivot pins 45 a and 45 b (i.e., pivot point) relative to the longitudinal axis “A-A” of the driving flanges 47 a and 47 b. In other words, by positioning the pivot pins 29 a and 29 b above the driving flanges 47 a and 47 b, the user gains lever-like mechanical advantage to actuate the jaw members 110 and 120. This reduces the overall amount of mechanical force necessary to close the jaw members 110 and 120 to affect a tissue seal. A similar mechanical arrangement is disclosed in commonly-owned U.S. patent application Ser. No. 10/460,926 the entire contents of which are incorporated by reference herein.

Handle 40 also includes a finger loop 43 which defines opening 41 which is dimensioned to facilitate grasping the handle 40. In one embodiment, finger loop 43 includes a rubber insert which enhances the overall ergonomic “feel” of the handle member 40. A locking flange 49′ is disposed on the outer periphery of the handle member 40 above the finger loop 43. Locking flange 49′ may be designed as a safety lock out mechanism to prevent the trigger assembly 70 from firing when the handle member 40 is oriented in a non-actuated position, i.e., the jaw members 110 and 120 are open. As can be appreciated, this would prevent accidental or premature severing of tissue prior to completion of the tissue seal.

Fixed handle 50 includes halves 50 a and 50 b which, when assembled, form handle 50. Fixed handle 50 includes a channel 51 defined therein which is dimensioned to receive flange 42 in a proximal moving manner when movable handle 40 is actuated. The t-shaped pin 44 of handle 40 is dimensioned for facile reception within channel 51 of handle 50. It is envisioned that flange 42 may be dimensioned to allow a user to selectively, progressively and/or incrementally move jaw members 110 and 120 relative to one another from the open to closed positions. For example, it is also contemplated that flange 42 may include a ratchet-like interface which lockingly engages the movable handle 40 and, therefore, jaw members 110 and 120 at selective, incremental positions relative to one another depending upon a particular purpose. Other mechanisms may also be employed to control and/or limit the movement of handle 40 relative to handle 50 (and jaw members 110 and 120) such as, e.g., hydraulic, semi-hydraulic, linear actuator(s), gas-assisted mechanisms and/or gearing systems.

As best illustrated in FIGS. 5D and 12, housing halves 20 a and 20 b when assembled form an internal cavity 52 which predefines the channel 51 within fixed handle 50 adjacent the railway 55 which reciprocates t-shaped pin 44 therein. Once assembled, the railway 55 is seated within cavity 52 in registration with entrance pathway 51 for reciprocation of the flange 42. Flange 42 and the housing halves 20 a and 20 b are designed to facilitate accurate and consistent reception of the t-shaped pin 44 into railway 55.

During movement of the flange 42 along the entrance to channel 51, the t-shaped pin 44 rides through passage 53 along railway 55 and is forced into a catch basin or seat 55′ to lock the handle 40 relative to handle 50. When the user releases the handle 40, the catch basin 55′ retains the t-shaped pin 44 in a secured position relative to the handle 50 as explained in further detail below. Railway 55 may be seated on one or pivot elements 55 a which allows the railway 55 to pivot upon reception of the t-shaped pin 44 therethrough. A spring element 57 biases the railway 55 to return to the original reception position once the t-shaped pin 44 is seated. The railway 55, gain, may pivot in response to release of the t-shaped pin 44 from catch basin 55′. It is envisioned that actuation of the handle 40 along with the inter-cooperating elements of the drive assembly 130 close the jaw members 110 and 120 about tissue with a pre-determinable and consistent closure pressure to affect a tissue seal. As mentioned above, closure pressures for sealing large tissue structures preferably fall within the range of about 3 kg/cm² to about 16 kg/cm².

When handle 40 is regrasped, the t-shaped pin 44 is forced out of or disengaged from the catch basin 55′ and moves along an exit pathway to release handle 40 from channel 51. A spring or other biasing member 57 may be employed to facilitate securing the flange 42 within the catch basin 55′ and also configured to facilitate release of the flange 42 from catch basin 55, upon re-grasping of the handle 40.

As explained in more detail below, once actuated, handle 40 moves in a generally arcuate fashion towards fixed handle 50 about pivot pins 45 a and 45 b which forces driving assembly 130 proximally which, in turn, pulls reciprocating sleeve 134 in a generally proximal direction to close jaw members 110 and 120 relative to one another.

As best shown in FIGS. 5A, 5B and 11, the drive assembly 130 mounts atop the proximal portion of the drive sleeve 134. A pair of retaining rings or clips 131′ and 131″ (See FIG. 11) cooperate with a corresponding pair of relieved portions 133 a and 133 b disposed on the drive sleeve 134 to mount the drive assembly 130 atop the drive sleeve 134 such that relative movement of the drive assembly correspondingly moves the drive sleeve 134. As handle 40 pivots about pivot point 45 and moves relative to handle 50 and flange 42 is incorporated into channel 51 of fixed handle 50, the driving flanges 47 a and 47 b, through the mechanical advantage of the above-the-center pivot point, force the drive assembly 130 proximally against spring 131.

As a result thereof, drive sleeve 134 reciprocates proximally which, in turn, closes the jaw members 110 and 120. It is envisioned that the utilization of an over-the-center pivoting mechanism will enable the user to selectively compress the coil spring 131 a specific distance which, in turn, imparts a specific load on the reciprocating sleeve 134 which is converted to a rotational torque about the jaw pivot pin 95. As a result, a specific closure force can be transmitted to the opposing jaw members 110 and 120.

FIGS. 5A and 5B show the initial actuation of handle 40 towards fixed handle 50 which causes the pin 44 of flange 42 to move generally proximally and upwardly along entrance pathway 51. During movement of the flange 42 along the entrance pathway 51, respectively, the t-shaped pin 44 rides through passageway 53 along railway 55 as explained above. Once the desired position for the sealing site is determined and the jaw members 110 and 120 are properly positioned, handle 40 may be compressed fully such that the t-shaped pin 44 of flange 42 seats within catch basin 55′. Once pin 44 clears an edge or passes a predetermined point in the passageway 53 at the edge of the catch basin 55′, releasing movement of the handle 40 and flange 42 is redirected into a catch basin 55′.

More particularly, upon a slight reduction in the closing pressure of handle 40 against handle 50, the handle 40 returns slightly distally towards entrance pathway 51 but is re-directed to seat within catch basin 55′. At this point, the release or return pressure between the handles 40 and 50 which is attributable and directly proportional to the release pressure associated with the compression of the drive assembly 130 causes the pin 44 of flange 42 to settle or lock within catch basin 55′. Handle 40 is now secured in position within fixed handle 50 which, in turn, locks the jaw members 110 and 120 in a closed position against the tissue.

As mentioned above, the jaw members 110 and 120 may be opened, closed and rotated to manipulate tissue until sealing is desired. This enables the user to position and re-position the forceps 10 prior to activation and sealing. As illustrated in FIG. 1A, the end effector assembly 100 is rotatable about longitudinal axis “A-A” through rotation of the rotating assembly 80. As explained in more detail below, it is envisioned that the unique feed path of the cable leads 325 a and 325 b through the rotating assembly 80, along shaft 12 and, ultimately, to the jaw members 110 and 120 enables the user to rotate the end effector assembly 100 about 180 degrees across the clockwise and counterclockwise directions without tangling or causing undue strain on cable leads 325 a and 325 b. As can be appreciated, this facilitates the grasping and manipulation of tissue.

As best shown in FIGS. 5A, 5B, 6A, 9A, 9B, 11 and 12, trigger assembly 70 mounts atop movable handle 40 and cooperates with the knife assembly 160 to selectively translate knife 190 through a tissue seal. More particularly, the trigger assembly 70 includes a U-shaped finger actuator 71 having a pair upwardly-extending flanges 71 a and 71 b. A pivot pin 179 extends through a pair of apertures 162 a and 162 b in each of the flanges 71 a and 71 b, respectively, to mount the trigger assembly 70 to a knife carriage 165 as explained in more detail below. Finger actuator 71 is selectively pivotable within a pre-defined slot 21 disposed within housing 20 (See FIG. 6A). More particularly, a pair of pivots 77 a and 77 b is disposed on either side of the finger actuator 71 and are configured to mount between housing halves 20 a and 20 b to pivot the finger actuator within slot 21.

The knife assembly 160 includes a reciprocating knife bar 167 which mounts atop the drive sleeve 134 and between upwardly extending flanges 71 a and 71 b. Knife bar 167 includes a t-shaped proximal end 167′ and a cuff 137 disposed at the distal end thereof. Cuff 137 is dimensioned to encapsulate drive sleeve 134 when the knife assembly 160 is assembled. A spring 76 biases the cuff in a proximal-most orientation. Proximal end 167′ is dimensioned to mount and slidingly reciprocate within a slot 167″ formed by housings 20 a and 20 b at assembly (See FIG. 12). A locking cap 137 a and a mounting pin 179 secure the cuff 137 to the proximal end 193 b of the knife rod 193 through aperture 197 disposed therein such that proximal movement to the finger actuator 71 results in distal movement of the knife bar 193. Cuff 137 and cap 137 a also allow 360 degrees of rotation of the drive sleeve 134 therethrough.

As mentioned above, a knife carriage 165 mounts to the upwardly extending flanges 71 a and 71 b of the finger actuator 71. More particularly, the distal end 162 of the knife carriage 165 is t-shaped and includes two laterally extending pins 162 c and 162 d which engage apertures 162 a and 162 b, respectively, in flanges 71 a and 71 b. The proximal end 161 of the knife carriage 165 includes an aperture 161 a defined therein which mates with a detent 167 a which extends transversally through knife carriage 165.

As best illustrated in FIGS. 5A-7, when the handle 40 is disposed in a spaced-apart or open configuration relative to handle 50, flange 49′ which extends from handle 40 prevents actuation of the trigger assembly 70. More particularly, finger actuator 71 is prevented from being actuated proximally by flange 49′ when the jaw members 110 and 120 are open. As can be appreciated, this prevents premature actuation of the knife 190 when tissue is not grasped between jaw members 110 and 120. When handle 40 is selectively moved relative to handle 50, a gap 21 is formed between the flange 49′ and the finger actuator 71 (See FIG. 5B). Thus, the user is free to selectively actuate the knife 190 by squeezing the finger actuator 71 proximally within gap 21.

As best shown in FIGS. 6B, 7 and 8A, once the clearance is provided by movement of handle 40, proximal movement of the finger actuator 71 about pivot 74 results in distal translation of the knife bar 167 which, in turn, results in distal translation of the knife rod 193 and knife 190. More particularly, when finger actuator 71 is squeezed proximally, the U-shaped flanges 71 a and 71 b rotate about pivot 74 to abut cuff 137 and essentially throw the knife carriage 165 forward which, in turn, carries the knife bar 167 forward to force the knife rod 193 distally. Slot 167″ is configured to smoothly guide the knife bar 167 distally through the forward and return stroke. As shown in FIGS. 10A and 10BC, distal translation of the knife rod 193 translates the knife 190 through channel 115 in the jaw members 110 and 120.

As mentioned above, the knife rod 193 mounts the knife 190 via one or more mechanically interfacing elements or may be affixed in any known manner in the art. A slot 197 defined within the knife 190 provides clearance for pin 139 of the drive sleeve 134 during reciprocation of the knife 190. Upon release of finger actuator 71, spring 76 biases the knife assembly back to a proximal-most position. It is envisioned that the knife bar 167 provides variable mechanical advantage and linear advantage when triggering the knife 190. In addition, the incorporation of the knife bar 167 significantly reduces friction loss and provides smoother mechanical cutting than previously known methods.

Turning now in detail to the operation of the drive assembly as best seen in FIGS. 5A, 5B, 11 and 12, drive assembly 130 includes reciprocating sleeve 134, drive housing 135, spring 131, drive rings 135 a and 135 b, drive stops 135 c and 135 d and retaining rings 131′ and 131″ which all cooperate to form the drive assembly 130. It is envisioned that stop 135 c may be removed and ring 131″ would perform stop 135 c's intended function. The proximal end 132 of the reciprocating sleeve 134 is positioned within an aperture 135′ defined through the drive housing 135 to permit selective reciprocation of the drive sleeve 134 therethrough upon actuation of the movable handle 40. The spring 131 is assembled atop the drive housing 135 between a rear stop 135 d and ring 135 b such that movement handle 40 about pivot 45 moves the entire drive assembly 130 and sleeve 134 proximally which, in turn, pulls cam pin 139 proximally to close the jaw members 110 and 120.

Once the jaw members 110 and 120 close about tissue, the drive assembly 130 essentially bottoms out (i.e., further proximal movement of the reciprocating sleeve is prevented) and further movement of handle 40 about pivot 45 compresses spring 131 resulting in additional closure force on the tissue. Moreover, spring 131 also tends to bias the jaw members 110 and 120 and the movable handle 40 in an open configuration.

Turning back to FIG. 12 which shows the exploded view of the housing 20, rotating assembly 80, trigger assembly 70, movable handle 40 and fixed handle 50, it is envisioned that all of these various component parts along with the shaft 12 and the end effector assembly 100 are assembled during the manufacturing process to form a partially and/or fully disposable forceps 10. For example and as mentioned above, the shaft 12 and/or end effector assembly 100 may be disposable and, therefore, selectively/releasably engageable with the housing 20 and rotating assembly 80 to form a partially disposable forceps 10 and/or the entire forceps 10 may be disposable after use.

As best seen in FIGS. 5A, 5B and 13, once assembled, spring 131 is poised for compression atop drive housing 135 upon actuation of the movable handle 40. More particularly, movement of the handle 40 about pivot pins 45 a and 45 b reciprocates the flange 42 into fixed handle 50 and forces drive assembly 130 to compress spring 131 against the rear stop 135 d to reciprocate the sleeve 134.

As mentioned above, the trigger assembly 70 is initially prevented from firing by the locking flange 491 disposed on movable handle 40 which abuts against the trigger assembly 70 prior to actuation. It is envisioned that the opposing jaw members 110 and 120 may be rotated and partially opened and closed without unlocking the trigger assembly 70 which, as can be appreciated, allows the user to grip and manipulate the tissue without premature activation of the knife assembly 160. As mentioned below, only when the t-shaped pin 44 of flange 42 is completely reciprocated within channel 51 of the fixed handle 50 and seated within pre-defined catch basin 55′ will the locking flange 49′ allow full activation of the trigger assembly 70. The operating features and relative movements of these internal working components of the forceps 10 are shown by phantom representation and directional arrows and are best illustrated in the various figures.

It is envisioned that the mechanical advantage of the over-the-center pivot will enable the user to selectively compress the coil spring 131 a specific distance which, in turn, imparts a specific load on the reciprocating sleeve 134. The reciprocating sleeve's 134 load is converted to a torque about the jaw pivot 95. As a result, a specific closure force can be transmitted to the opposing jaw members 110 and 120. As mentioned above, the jaw members 110 and 120 may be opened, closed and rotated to manipulate tissue until sealing is desired without unlocking the trigger assembly 70. This enables the user to position and re-position the forceps 10 prior to activation and sealing. More particularly, as illustrated in FIG. 1A, the end effector assembly 100 is rotatable about longitudinal axis “A-A” through rotation of the rotating assembly 80.

Once the desired position for the sealing site is determined and the jaw members 110 and 120 are properly positioned, handle 40 may be compressed fully such that the t-shaped pin 44 of flange 42 clears a pre-defined railway edge located atop the railway 55. Once end 44 clears the railway edge, the end 44 is directed into catch basin 55′ to lock the handle 40 relative to handle 50. The release or return pressure between the handles 40 and 50 which is attributable and directly proportional to the release pressure associated with the compression of the drive assembly 130 causes the end 44 of flange 42 to settle or lock within catch basin 55′, Handle 40 is now secured in position within fixed handle 50 which, in turn, locks the jaw members 110 and 120 in a closed position against the tissue.

At this point the jaws members 110 and 120 are fully compressed about the tissue. Moreover, the forceps 10 is now ready for selective application of electrosurgical energy and subsequent separation of the tissue, i.e., as t-shaped end 44 seats within catch basin 55′, locking flange 49′ moves into a position to permit activation of the trigger assembly 70.

As the t-shaped end 44 of flange 42 seats within catch basin 55′, a proportional axial force on the reciprocating sleeve 134 is maintained which, in turn, maintains a compressive force between opposing jaw members 110 and 120 against the tissue. It is envisioned that the end effector assembly 100 and/or the jaw members 110 and 120 may be dimensioned to off-load some of the excessive clamping forces to prevent mechanical failure of certain internal operating elements of the end effector 100.

As can be appreciated, the combination of the mechanical advantage of the over-the-center pivot along with the compressive force associated with the compression spring 131 facilitate and assure consistent, uniform and accurate closure pressure about the tissue within the desired working pressure range of about 3 kg/cm² to about 16 kg/cm² and, desirably, about 7 kg/cm² to about 13 kg/cm². By controlling the intensity, frequency and duration of the electrosurgical energy applied to the tissue, the user can treat tissue, i.e., seal tissue.

As mentioned above, two mechanical factors play an important role in determining the resulting thickness of the sealed tissue and effectiveness of the seal, i.e., the pressure applied between opposing jaw members 110 and 120 and the gap distance “G” between the opposing sealing surfaces 112, 122 of the jaw members 110 and 120 during the sealing process. However, thickness of the resulting tissue seal cannot be adequately controlled by force alone. In other words, too much force and the two jaw members 110 and 120 would touch and possibly short resulting in little energy traveling through the tissue thus resulting in a bad tissue seal 450. Too little force and the seal would be too thick.

Applying the correct force is also important for other reasons: to oppose the walls of the vessel; to reduce the tissue impedance to a low enough value that allows enough current through the tissue; and to overcome the forces of expansion during tissue heating in addition to contributing towards creating the required end tissue thickness which is an indication of a good seal.

In one embodiment, the electrically conductive sealing surfaces 112 and 122 of the jaw members 110 and 120, respectively, are relatively flat to avoid current concentrations at sharp edges and to avoid arcing between high points. In addition and due to the reaction force of the tissue when engaged, jaw members 110 and 120 can be manufactured to resist bending. For example, the jaw members 110 and 120 may be tapered along the width thereof which is advantageous for two reasons: 1) the taper will apply constant pressure for a constant tissue thickness at parallel; 2) the thicker proximal portion of the jaw members 110 and 120 will resist bending due to the reaction force of the tissue.

As mentioned above, at least one jaw member, e.g., 120, may include one or more stop members 90 which limit the movement of the two opposing jaw members 110 and 120 relative to one another. In one embodiment, the stop members 90 extend from the sealing surface 122 a predetermined distance according to the specific material properties (e.g., compressive strength, thermal expansion, etc.) to yield a consistent and accurate gap distance “G” during sealing (FIG. 10B). It is envisioned for the gap distance between opposing sealing surfaces 112 and 122 during sealing ranges from about 0.001 inches to about 0.006 inches and, desirably, between about 0.002 and about 0.005 inches.

In one embodiment, the non-conductive stop members 90 are molded onto the jaw members 110 and 120 (e.g., overmolding, injection molding, etc.), stamped onto the jaw members 110 and 120 or deposited (e.g., deposition) onto the jaw members 110 and 120. For example, one technique involves thermally spraying a ceramic material onto the surface of the jaw member 110 and 120 to form the stop members 90. Several thermal spraying techniques are contemplated which involve depositing a broad range of heat resistant and insulative materials on various surfaces to create stop members 90 for controlling the gap distance between electrically conductive surfaces 112 and 122.

As energy is being selectively transferred to the end effector assembly 100, across the jaw members 110 and 120 and through the tissue, a tissue seal forms isolating two tissue halves. At this point and with other known vessel sealing instruments, the user may remove and replace the forceps 10 with a cutting instrument (not shown) to divide the tissue halves along the tissue seal. As can be appreciated, this is both time consuming and tedious and may result in inaccurate tissue division across the tissue seal due to misalignment or misplacement of the cutting instrument along the ideal tissue cutting plane.

As explained in detail above, the present disclosure incorporates knife assembly 160 which, when activated via the trigger assembly 70, progressively and selectively divides the tissue along an ideal tissue plane in a precise manner to effectively and reliably divide the tissue into two sealed halves. The knife assembly 160 allows the user to quickly separate the tissue immediately after sealing without substituting a cutting instrument through a cannula or trocar port. As can be appreciated, accurate sealing and dividing of tissue is accomplished with the same forceps 10.

It is envisioned that knife blade 190 may also be coupled to the same or an alternative electrosurgical energy source to facilitate separation of the tissue along the tissue seal. Moreover, it is envisioned that the angle of the trip of the knife blade 190 may be dimensioned to provide more or less aggressive cutting angles depending upon a particular purpose. For example, the knife blade 190 may be positioned at an angle which reduces “tissue wisps” associated with cutting. Moreover, the knife blade 190 may be designed having different blade geometries such as serrated, notched, perforated, hollow, concave, convex etc. depending upon a particular purpose or to achieve a particular result. It is envisioned that the knife assembly 160 generally cuts in a progressive, uni-directional fashion (i.e., distally).

Once the tissue is divided into tissue halves, the jaw members 110 and 120 may be opened by re-grasping the handle 40 as explained below. Re-initiation or re-grasping of the handle 40 again moves t-shaped pin 44 of flange 42 generally proximally.

As best shown in FIG. 13, the proximal portions of the jaw members 110 and 120 and the distal end 16 of shaft 12 may be covered by a resilient or flexible insulating material 185 to reduce stray current concentrations during electrosurgical activation. The tail or proximal end of the jaw members 110 and 120 may be removed and covered with an extended section of the guide element 170 creating a semi insulative barrier to reduce stray current concentrations during electrosurgical activation. An insulating boot (not shown) may also be positioned atop the proximal portions of the jaw members 110 and 120 to further reduce current concentrations and stray currents from damaging adjacent tissue. Details relating to one envisioned insulating boot 220 are described with respect to commonly-owned U.S. Provisional Application Ser. No. 60/722,213 entitled “INSULATING BOOT FOR ELECTROSURGICAL FORCEPS”, the entire contents of which being incorporated by reference herein.

Switch 60 is ergonomically dimensioned and conforms to the outer shape of housing 20 (once assembled). Switch 60 is designed to electromechanically cooperate with a flex circuit 400 (See FIG. 6C) to allow a user to selectively activate the jaw members 110 and 120. It is contemplated that a flex circuit design facilitates manufacturing due to the circuit unique ability to conform as needed into tightly spaced areas. It is also envisioned that the switch 60 permits the user to selectively activate the forceps 10 in a variety of different orientations, i.e., multi-oriented activation or toggle-like activation. As can be appreciated, this simplifies activation. It is envisioned that switch 60 may also be designed as a so called “dome switch” which also provides tactile feedback to the user when activated.

When switch 60 is depressed, trigger lead 310 b carries the first electrical potential to jaw member 110 thus completing a bipolar circuit. More particularly, when switch 60 is depressed and flex circuit 400 is activated, the generator recognizes a voltage drop across leads 310 a and 310 c which initiates activation of the generator to supply a first electrical potential to jaw member 110 and a second electrical potential to jaw member 120. Switch 60 acts as a control circuit and is protected or removed from the actual current loop which supplies electrical energy to the jaw members 110 and 120. This reduces the chances of electrical failure of the switch 60 due to high current loads during activation. A footswitch (not shown) which may also be utilized with the forceps 10, also operates in a similar manner, i.e., upon activation of the footswitch, the generator recognizes a voltage drop across the input and output leads of the footswitch which, in turn, signals the generator to initiate electrosurgical activation of the jaw members 110 and 120.

It is envisioned that a safety switch or circuit (not shown) may be employed such that the switch cannot fire unless the jaw members 110 and 120 are closed and/or unless the jaw members 110 and 120 have tissue held there between.

In the latter instance, a sensor (not shown) may be employed to determine if tissue is held therebetween. In addition, other sensor mechanisms may be employed which determine pre-surgical, concurrent surgical (i.e., during surgery) and/or post surgical conditions. The sensor mechanisms may also be utilized with a closed-loop feedback system coupled to the electrosurgical generator to regulate the electrosurgical energy based upon one or more pre-surgical, concurrent surgical or post surgical conditions. Various sensor mechanisms and feedback systems are described in commonly-owned, co-pending U.S. patent application Ser. No. 10/427,832 entitled “METHOD AND SYSTEM FOR CONTROLLING OUTPUT OF RF MEDICAL GENERATOR” filed on May 1, 2003 the entire contents of which are hereby incorporated by reference herein.

The conductive surfaces 115 a and 115 b are electrically isolated from one another and jaw members 110 and 120 such that electrosurgical energy can be effectively transferred through the tissue to form the seal. The cable leads 310 b and 325 b are held loosely but securely along the cable path to permit rotation of the jaw members 110 and 120 about longitudinal axis “A” (See FIG. 1A). More particularly, cable leads 310 b and 325 b are fed through respective halves 80 a and 80 b of the rotating assembly 80 in such a manner to allow rotation of the shaft 12 (via rotation of the rotating assembly 80) in the clockwise or counter-clockwise direction without unduly tangling or twisting the cable leads 310 b and 325 b. The presently disclosed cable lead feed path is envisioned to allow rotation of the rotation assembly approximately 180 degrees in either direction.

From the foregoing and with reference to the various figure drawings, those skilled in the art will appreciate that certain modifications can also be made to the present disclosure without departing from the scope of the same. For example, it may be preferable to add other features to the forceps 10, e.g., an articulating assembly to axially displace the end effector assembly 100 relative to the elongated shaft 12.

It is also contemplated that the forceps 10 (and/or the electrosurgical generator used in connection with the forceps 10) may include a sensor or feedback mechanism (not shown) which automatically selects the appropriate amount of electrosurgical energy to effectively seal the particularly-sized tissue grasped between the jaw members 110 and 120. The sensor or feedback mechanism may also measure the impedance across the tissue during sealing and provide an indicator (visual and/or audible) that an effective seal has been created between the jaw members 110 and 120. Examples of such sensor systems are described in commonly-owned U.S. patent application Ser. No. 10/427,832 entitled “METHOD AND SYSTEM FOR CONTROLLING OUTPUT OF RF MEDICAL GENERATOR” filed on May 1, 2003 the entire contents of which are hereby incorporated by reference herein.

Moreover, it is contemplated that the trigger assembly 70 may include other types of recoil mechanism which are designed to accomplish the same purpose, e.g., gas-actuated recoil, electrically-actuated recoil (i.e., solenoid), etc. It is also envisioned that the forceps 10 may be used to cut tissue without sealing. Alternatively, the knife assembly 70 may be coupled to the same or alternate electrosurgical energy source to facilitate cutting of the tissue.

It is envisioned that the outer surface of the end effector assembly 100 may include a nickel-based material, coating, stamping, metal injection molding which is designed to reduce adhesion between the jaw members 110 and 120 with the surrounding tissue during activation and sealing. Moreover, it is also contemplated that the conductive surfaces 112 and 122 of the jaw members 110 and 120 may be manufactured from one (or a combination of one or more) of the following materials: nickel-chrome, chromium nitride, MedCoat 2000 manufactured by The Electrolizing Corporation of OHIO, inconel 600 and tin-nickel. The tissue conductive surfaces 112 and 122 may also be coated with one or more of the above materials to achieve the same result, i.e., a “non-stick surface”. As can be appreciated, reducing the amount that the tissue “sticks” during sealing improves the overall efficacy of the instrument.

One particular class of materials disclosed herein has demonstrated superior non-stick properties and, in some instances, superior seal quality. For example, nitride coatings which include, but not are not limited to: TiN, ZrN, TiAlN, and CrN are preferred materials used for non-stick purposes. CrN has been found to be particularly useful for non-stick purposes due to its overall surface properties and optimal performance. Other classes of materials have also been found to reducing overall sticking. For example, high nickel/chrome alloys with a Ni/Cr ratio of approximately 5:1 have been found to significantly reduce sticking in bipolar instrumentation. One particularly useful non-stick material in this class is Inconel 600. Bipolar instrumentation having sealing surfaces 112 and 122 made from or coated with Ni200, Ni201 (˜100% Ni) also showed improved non-stick performance over typical bipolar stainless steel electrodes.

As can be appreciated, locating the switch 60 on the forceps 10 has many advantages. For example, the switch 60 reduces the amount of electrical cable in the operating room and eliminates the possibility of activating the wrong instrument during a surgical procedure due to “line-of-sight” activation. Moreover, it is also envisioned that the switch 60 may be configured such that it is mechanically or electro-mechanically decommissioned during trigger activation to eliminate unintentionally activating the device during the cutting process. It is also envisioned that the switch 60 may be disposed on another part of the forceps 10, e.g., the fixed handle 50, rotating assembly 80, housing 20, etc.

It is also envisioned that the forceps 10 may be equipped with an automatic, electro-mechanical release mechanism (not shown) which releases the tissue once an end seal is determined (i.e., end-tone signal from the generator). For example, an electromechanical interface may be configured to automatically release the t-shaped pin 44 from catch basin 55 upon an end tone condition.

It is also contemplated that the forceps 10 may be dimensioned to include a trigger assembly 70 which operates in lieu of the switch assembly 60 to activate the forceps to seal tissue while also advancing the knife 190 to divide the tissue across the seal. For example, the trigger assembly 70 could be configured to have two stages: a first or initial stroke stage which activates the generator to selectively seal tissue; and a second or subsequent stage which advances the knife through the tissue. Alternatively, another embodiment may include a trigger assembly which simultaneously activates the jaw members 110 and 120 to seal tissue and advances the knife 190 through the tissue during activation.

It is also envisioned that the rotating assembly 80 may be equipped with one or more mechanical interfaces which are rotatable with or within the rotating assembly 80 and which are configured to produce tactile and/or audible feedback to the user during rotation. The tactile and/or audible feedback (i.e., a “click”) may be configured to correspond to a particular degree of rotation of the end effector assembly 100 about the axis “A”. It is also contemplated that one or more types of visual indicia may also be employed with the rotating assembly 80 to correspond to the amount or degree of rotation of the end effector assembly 100 and may be designed correspond to or relate to the audible and/or tactile feedback depending upon a particular purpose.

Another envisioned version of the forceps 10 may include a telescoping shaft which allows the user to selectively regulate the length of the instrument for particular surgical purposes. For example, it is envisioned that the shaft may include two slidingly reciprocatable and extendible elements which upon exertion (i.e., pulling, twisting, or by virtue of a mechanical lever on the handle) either lengthen or shorten the size of the elongated shaft 12 depending upon a particular surgical purpose.

Moreover, it is also contemplated that the diameter of shaft 12 may be selectively expandable depending upon a particular surgical purpose or to provide rigidity of the forceps 10 inside the surgical cavity or to enhance the sealing effect of the shaft through a trocar. More particularly, it is contemplated that the shaft 12 may be configured to expand upon exertion (i.e., twisting or rotating one element inside another (iris-like), sliding a mechanical lever, an inflatable system, a mechanically expanding system or other types of known expansion systems). As a result, the surgeon can selectively expand the outer diameter of the shaft 12 to enhance the rigidity of the shaft 12 within a trocar and/or enhance the sealing effect of the shaft 12 within the trocar to reduce the possibility of pressure leakage from surgical cavity during use. Moreover, a single forceps may be selectively adaptable to work with differently-sized trocars and/or cannulas which may prove advantageous for particular operations and other surgical procedures.

It is also contemplated that the forceps 10 may be configured such that handle 50 is selectively replaceable or selectively positionable depending upon user preference. For example, handle 50 may be selectively detached and replaced with another handle 50 which is of different dimension (i.e., size, weight, angle, orientation to user's hand, etc.) which facilitates handling during surgical procedures. Alternatively, handle 50 may be selectively positionable relative to the housing 20 (i.e., the angle of the handle to the housing is adjustable) to facilitate handling and use during particular surgical procedures or for user comfort.

It is also envisioned that the forceps may be configure to include a visual indicator (which cooperates with the “end tone” indicator on the generator) to provide visual confirmation of a successful seal (e.g., a green LED indicator). The visual indicator (not shown) may be employed on or in connection with the end effector assembly 100 or shaft 12 which is in line-of-site of the surgeon during use. The visual indicator may also be designed to warn the user of a mis-seal condition or a re-grasp condition (e.g., a red LED indicator). Alternatively, the visual indicator may also be configured to provide progressive feedback of the formation of the seal during the sealing process. For example, a series of LEDs may be employed on the end effector assembly 100 (or shaft 12) which progressively illuminate through the sealing process to provide visual feedback to the user regarding the status of the seal. Moreover, it is envisioned that one or both jaw members may include visual markings which indicate the end of a seal and/or the length of the seal cut.

It is also envisioned that the guide element 170 (See FIG. 14) may be configured to not only guide the knife 190 into the knife channel 115 disposed between the jaw members 110 and 120, but may also be dimensioned to precisely space the jaw members 110 and 120 relative to one another about the pivot 95. Moreover, the guide element 170 may be configured to include one or more grooves of tracks (not shown) to guide the electrical connections or wires 310 b and 325 b through the end effector assembly 100. The guide element 170 may also be configured to limit the distal movement of the drive rod 193 for the knife 190 which, in turn, limits the overall travel of the knife 190 through the knife channel 115. The distal end of the guide element may be extended to work with the overmolded jaw elements 116 and 126 to create a set of tissue blocking features which inhibit tissue from getting behind or moving proximal to the active electrode surface.

It is also contemplated that the stem 95 a of the pivot pin 95 may include a stepped diameter which securely compresses the jaw members 110 and 120 together when mechanically secured with the cap 95 b. Moreover, the pivot may be dimensioned to include a pass through or aperture 96 which allows translation of the knife therethrough. The two-piece pivot 95 including stem 95 a and cap 95 b may be assembled during the manufacturing process by any one of several known manufacturing techniques including: laser or heat-based welding, press-fit mechanical interaction (or other mechanically interlocking geometry, adhesives, chemical bonding, etc.

It is also envisioned that the shaft may be dimensioned to enhance visibility and/or non-symmetric depending upon a particular purpose. For example, it is contemplated that the shaft may be generally oval in dimension thereby providing uni-directional strength in one dimension versus another and maximized visibility to the operating site in one direction versus another. Alternatively, the shaft may be other geometric configurations depending upon a particular purpose, I-beam, square, polygonal, etc.

It is also envisioned that the end effector assembly 100 is optimized for reengaging long tissue sections and visibility of the operating site. The jaw members 110 and 120 may also be dimensioned to include distal ends configured for gross or blunt dissection.

FIGS. 15A-15M show various examples of different cutting assemblies and/or blade assemblies which may be utilized to divide the tissue after the tissue seal is complete (or divide tissue without sealing depending upon a particular purpose). For example, FIG. 15A shows a guillotine-like cutting assembly 500 disposed within the upper jaw member 510 for use in dividing tissue. More particularly, once tissue is positioned between sealing surfaces 512 and 522 of jaw members 510 and 520, respectively, cutting assembly 500 may be selectively actuated to divide the tissue. Cutting assembly 500 includes a cutting blade 515 which mechanically cooperates with a ramp surface 523 to divide tissue upon proximal movement of the blade 515. Blade 515 is initially positioned at a point distal to the ramp surface 523 such that the blade 515 is at least partially recessed within jaw member 510 to allow selective tissue sealing. Proximal movement of an actuator or rod 524 moves the blade 515 proximally against ramp surface 523 and cams the blade 515 inwardly to extend a distance from the sealing surface 512 to divide tissue disposed between the jaw members. A return spring 525 may be utilized to bias the blade 515 in a distal-most, partially recessed position.

FIG. 15B shows another cutting assembly 600 for use with the forceps 10. More particularly, once tissue is positioned between sealing surfaces 612 and 622 of jaw members 610 and 620, respectively, cutting assembly 600 may be selectively actuated to divide the tissue. Cutting assembly 600 includes a pair of blades 615 a and 615 b arranged in a scissor-like fashion about a pivot 616. Movement of actuator 627 operates the blades 615 a and 615 b from an open to closed position for cutting tissue. Movement of rod 625 positions the cutting assembly 600 between the jaw members 610 and 620 for cutting tissue.

FIG. 15C shows yet another embodiment of a cutting assembly 700 for use with forceps 10. Cutting assembly 700 includes a v-shaped wedge 715 which is disposed between jaw members 710 and 720 near a proximal-most portion thereof. It is envisioned that the v-shaped wedge 715 extends between sealing surfaces 712 and 722 and is substantially pliable to allow the jaw members 710 and 720 to close about tissue. Once the tissue is sealed or otherwise treated, the jaw members 710 and 720 are opened to “unfold” or otherwise bias the v-shaped wedge 715 into a cutting orientation. The forceps 10 is then advanced or pushed distally to force tissue between the jaw members 710 and 720. The leading edge of the v-shaped wedge 715 divides the tissue along a preferred cutting plane as the forceps 10 is pushed distally through the tissue.

FIG. 15D shows yet another cutting assembly 800 which includes a heating element or so-called “hot wire” 827 which is selectively advanced through tissue disposed between jaw members 810 and 820. More particularly, cutting assembly 800 includes a selectively advanceable heating element 827 which is heated prior to actuation or movement thereof such that when advanced distally, the heating element 827 divides tissue disposed between the jaw members 810 and 820. The heating element 827 may be heated resistively, conductively or in other ways known in the art. A remote actuator 825 may be utilized to deploy the heating element 827 to divide tissue.

FIG. 15E shows another embodiment of a cutting assembly 900 which includes an ultrasonically energize blade 925 which may be selectively advanced to divide tissue disposed between the jaw members 910 and 920. More particularly, the cutting assembly 900 includes an ultrasonic transducer 927 which is disposed within the forceps 10 and which is configured to ultrasonically energize blade 925. Blade 925 may then be selectively advanced through the tissue disposed between jaw members 910 and 920.

FIG. 15F shows another embodiment of a cutting assembly 1000 for use with the presently disclosed forceps 10. More particularly, cutting assembly 1000 includes a partially recessed blade 1025 disposed in the side of jaw member 1010. Once the tissue has been treated, the jaw members 1010 and 1020 are rotated in the direction of arrow “R” such that the leading edge of the blade 1025 cuts tissue. It is envisioned that the blade 1025 may be selectively extendible from the side of the jaw member 1010 to mitigate any safety concerns during the sealing and manipulation of tissue.

FIG. 15G shows yet another embodiment of a cutting assembly 1100 for use with forceps 10. Cutting assembly 1100 includes a pair of blade members 1125 a and 1125 b disposed in the upper and lower jaws 1110 and 1120, respectively. The blades 1125 a and 1125 b are configured to each include a flange-like element 1126 a and 1126 b, respectively, which extends beyond the outer peripheral surface of each jaw member 1110 and 1120. The flanges 1126 a and 1126 b are each rotatable about a corresponding pivot 1127 a and 1127 b disposed near the proximal end of each jaw member 1110 and 1120. A camming element or sleeve 1127 is selectively actuatable via actuator rod 1129 to extend distally over the jaw members 1110 and 1120 (when disposed in the closed position) to cam the flanges 1126 a and 1126 b inwardly about pivots 1127 a and 1127 b to divide tissue disposed between the jaw members 1110 and 1120.

FIG. 15H shows a screw-like cutting assembly 1200 which is selectively advanceable between jaw members 1210 and 1220 to divide the tissue. More particularly, an actuator 1229 selectively advances a rotating mulcher or morcellator 1125 through tissue disposed between the jaw members 1210 and 1220 after the tissue is treated. In this instance, the mulcher essentially chews or bores through tissue disposed between the jaw members 1210 and 1220 to divide the tissue along a preferred cutting plane.

FIG. 15I shows a perforating cutting assembly 1300 for use with forceps 10. More particularly, cutting assembly 1300 includes a cutting blade 1325 having a series of longitudinally-oriented knives or perforating sections 1324 disposed therealong generally extending from a proximal portion of jaw members 1310 to a distal end thereof. Cutting blade 1325 is moveable within jaw member 1310 from a first recessed position wherein the knives are recessed within sealing surface 1312 to an extended position wherein the knives extend beyond the sealing surface 1312. A cam 1327 is selectively actuatable via drive rod 1329 to move the cutting blade between the first and second positions to cut tissue disposed between jaw members 1310 and 1320. Upon actuation of the drive rod 1329, the knives 1324 are forced into the tissue to essentially perforate the tissue for subsequent separation along the perforation.

FIG. 15J shows yet another cutting assembly 1400 which includes a tooth-like or scythe-like cutter 1425 disposed within jaw member 1410. Proximal actuation of drive rod 1429 pulls the tooth-like cutter 1425 proximally from a recessed position within jaw member 1410 to an extended position (extended relative to sealing surface 1412) to divide the tissue disposed between the jaw members 1410 and 1420. A portion 1426 may be bent or configured accordingly to force or guide the tooth-like cutter 1425 along a preferred cutting plane.

FIG. 15K shows yet another cutting assembly 1500 which includes a pizza-like cutting wheel 1525 disposed within jaw member 1510. Pizza-like cutting wheel 1525 is movable via an actuating rod 1529 from a first recessed position to an extended position (extended relative to sealing surface 1512) within jaw member 1510, Jaw member 1510 includes a camming surface 1526 which guides the pizza-like cutter 1525 along a preferred cutting plane when pulled in a proximal direction.

FIG. 15L shows a laser cutting assembly 1600 for use with forceps 10 for dividing tissue. More particularly, a laser firing mechanism 1625 is disposed in jaw member 1610 and a mirror or optical absorbing plate 1627 is disposed in the opposite jaw member 1620. Upon activation, a remote energy source fires a laser through cable 1631 which is dispersed at jaw member 1610 into a perforating pattern to project a series of individual cutting lasers 1624 through tissue disposed between the jaw members 1610 and 1620. An absorption plate 1627 disposed in jaw member 1620 receives and diffuses the lasers 1624 after the lasers 1624 cut through the tissue to eliminate stray energy paths. The tissue is subsequently separated along the perforation.

FIG. 15M shows yet another embodiment of a cutting assembly 1700 for use with forceps 10. Cutting assembly 1700 includes a chain-saw-like cutter 1725 having a rotating chain 1726 including a plurality of sharp teeth 1726 b which rotate around a pair of gears 1729 a and 1729 b to cut tissue. More particularly, upon activation of a signal via lead 1731, chain 1726 is rotated longitudinally along jaw members 1710 around gears 1729 a and 1729 b. The upper portion of the chain 1726 remains recessed within jaw member 1710 while the lower portion is configured to extend past sealing plate 1712 to contact tissue when the jaw members 1710 and 1720 are closed about tissue.

While several embodiments of the disclosure have been shown in the drawings, it is not intended that the disclosure be limited thereto, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplifications of particular embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto. 

1. A bipolar forceps, comprising: a housing; a shaft affixed to the housing having jaw members at a distal end thereof, the shaft having a longitudinal axis defined therethrough, the jaw members adapted to connect to a source of electrosurgical energy such that the jaw members are capable of conducting energy through tissue held therebetween to effect a tissue seal; a drive assembly that moves the jaw members relative to one another from a first position wherein the jaw members are disposed in spaced relation relative to one another to a second position wherein the jaw members are closer to one another for manipulating tissue; a movable handle being rotatable about a pivot to force a drive flange of the drive assembly to move the jaw members between the first and second positions; and a cutting assembly including at least one blade element disposed within one of said jaw members, said blade element being selectively moveable from a first recessed position within said jaw member to a second extended position for cutting tissue, said cutting assembly including a remote actuator that reciprocates a camming element to move said at least one blade element between the first and second positions, wherein said actuator includes a sleeve that is selectively movable over said jaw members to cam said at least one blade element into tissue.
 2. A bipolar forceps according to claim 1 wherein said cutting assembly includes a spring that biases the at least one blade element in a recessed configuration.
 3. A bipolar forceps according to claim 1 further comprising a hand switch disposed within the housing and adapted to connect to the source of electrosurgical energy, the hand switch allowing a user to selectively supply bipolar energy to the jaw members to effect a tissue seal.
 4. A bipolar forceps according to claim 1 wherein at least one of the jaw members includes a series of stop members disposed thereon that are configured to regulate the distance between the jaw members during sealing. 